EP1792168B1 - Vorrichtung und verfahren für multimodale bilderzeugung - Google Patents

Vorrichtung und verfahren für multimodale bilderzeugung Download PDF

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Publication number
EP1792168B1
EP1792168B1 EP05797671.4A EP05797671A EP1792168B1 EP 1792168 B1 EP1792168 B1 EP 1792168B1 EP 05797671 A EP05797671 A EP 05797671A EP 1792168 B1 EP1792168 B1 EP 1792168B1
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EP
European Patent Office
Prior art keywords
imaging
image
immobilized
mode
phosphor plate
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EP05797671.4A
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English (en)
French (fr)
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EP1792168A1 (de
Inventor
Douglas Lincoln Vizard
Joel Norman Helfer
George Brocksieper
William E. Mclaughlin
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Carestream Health Inc
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Carestream Health Inc
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
    • A61B6/5229—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image
    • A61B6/5235—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4417—Constructional features of apparatus for radiation diagnosis related to combined acquisition of different diagnostic modalities
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/508—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for non-human patients

Definitions

  • the invention relates generally to the field of imaging systems, and more particularly to the imaging of objects. More specifically, the invention relates to an apparatus and method that enable analytical imaging of objects (for example, small animals and tissue) in differing modes, including bright-field, dark-field (e.g., luminescence and fluorescence), and x-ray and radioactive isotopes.
  • objects for example, small animals and tissue
  • dark-field e.g., luminescence and fluorescence
  • radioactive isotopes for example, radioactive isotopes.
  • An exemplary electronic imaging system (shown in Figure 1 and diagrammatically illustrated in Figure 2 ) is the Image Station 2000MM Multimodal Imaging System 10 available from the Eastman Kodak Company.
  • System 10 includes a light source 12, an optical compartment 14 which can include a mirror 16, a lens/camera system 18, and a communication/computer control system 20 which can include a display device, for example, a computer monitor 22.
  • Camera/lens system 18 can include an emission filter wheel for fluorescent imaging.
  • Light source 12 can include an excitation filter selector for fluorescent excitation or bright field color imaging, hi operation, an image of an object is captured using lens/camera system 18.
  • System 18 converts the light image into an electronic image, which can be digitized. The digitized image can be displayed on the display device, stored in memory, transmitted to a remote location, processed to enhance the image, and/or used to print a permanent copy of the image.
  • Applicants have recognized a need for an apparatus and method for enabling analytical imaging of an object in differing modes.
  • An object of the present invention is to provide an apparatus and method for enabling analytical imaging of an object.
  • Another object of the present invention is to provide such an apparatus and method for enabling analytical imaging of an object in differing modes.
  • an imaging system for imaging an object.
  • the imaging system includes a support member adapted to receive the object in an immobilized state.
  • the system also includes first means for imaging the immobilized object in a first imaging mode to capture a first image, and second means for imaging the immobilized object in a second imaging mode, different from the first imaging mode, to capture a second image.
  • the first imaging mode is selected from the group: x-ray mode and radio isotopic mode.
  • the second imaging mode is selected from the group: bright-field mode and dark-field mode.
  • a removable phosphor screen is employed when the first image is captured and not employed when the second image is captured.
  • the phosphor screen is adapted to transduce ionizing radiation to visible light.
  • the phosphor screen is adapted to be removable without moving the immobilized object.
  • the system can further include means for generating a third image comprised of the first and second image.
  • Applicants have recognized that the complex pharmaceutical analyses of small objects/subjects (e.g., small animal and tissue) images are particularly enhanced by using different in-vivo imaging modalities.
  • small objects/subjects e.g., small animal and tissue
  • precisely co-registered fluorescent, luminescent and/or isotopic probes within an object can be localized and multiple images can be accurately overlaid onto the simple bright-field reflected image or anatomical x- ray of the same animal within minutes of animal immobilization.
  • the present invention uses the same imaging system to capture differing modes of imaging, thereby enabling/simplifying multi-modal imaging.
  • the relative movement of probes can be kinetically resolved over the time period that the animal is effectively immobilized (which can be tens of minutes).
  • the same animal may be subject to repeated complete image analysis over a period of days/weeks required to assure completion of a pharmaceutical study, with the assurance that the precise anatomical frame of reference (particularly, the x-ray) may be readily reproduced upon repositioning the object animal.
  • the method of the present invention can be applied to other objects and/or complex systems subject to simple planar imaging methodologies.
  • an immobilized object can be imaged in several imaging modes without changing/moving the immobilized object. These acquired multi-modal images can then be merged to provide one or more co-registered image(s) for analysis.
  • Imaging modes supported by the apparatus/method of the present invention include: x-ray imaging, bright-field imaging, dark-field imaging (including luminescence imaging, fluorescence imaging) and radioactive isotope imaging. Images acquired in these modes can be merged in various combinations for analysis. For example, an x-ray image of the object can be merged with a near IR fluorescence image of the object to provide a new image for analysis.
  • Figure 3A shows a diagrammatic side view of an imaging system 100 in accordance with the present invention
  • Figure 3B shows a diagrammatic front view of imaging system 100
  • Figure 4 shows a perspective view of imaging system 100.
  • Imaging system 100 includes light source 12, optical compartment 14, a lens/camera system 18, and communication/computer control system 20 which can include a display device, for example, a computer monitor 22.
  • Camera/lens system 18 can include an emission filter wheel for fluorescent imaging.
  • Light source 12 can include an excitation filter selector for fluorescent excitation or bright field color imaging.
  • imaging system 100 includes an x-ray source 102 and a support member such as a sample object stage 104.
  • An immobilized object such as a mouse is received on and supported by sample object stage 104 during use of the system 100.
  • Imaging system 100 further comprises epi-illumination, for example, using fiber optics 106, which directs conditioned light (of appropriate wavelength and divergence) toward sample object stage 104 to provide bright-field or fluorescent imaging.
  • Sample object stage 104 is disposed within a sample environment 108, which allows access to the object being imaged.
  • sample environment 108 is light-tight and fitted with light-locked gas ports (not illustrated) for environmental control.
  • Environmental control enables practical x-ray contrast below 8 Kev (air absorption) and aids in life support for biological specimens. Such environmental control might be desirable for controlled x-ray imaging or for support of particular specimens.
  • Imaging system 100 can include an access means/member 110 to provide convenient, safe and light-tight access to sample environment 108, such as a door, opening, labyrinth, and the like. Additionally, sample environment 108 is preferably adapted to provide atmospheric control for sample maintenance or soft x-ray transmission (e.g., temperature/humidity/alternative gases and the like).
  • sample environment 108 is preferably adapted to provide atmospheric control for sample maintenance or soft x-ray transmission (e.g., temperature/humidity/alternative gases and the like).
  • Imaging system 100 can be a unitary system. Alternatively, imaging system 100 can be a modular unit adapted to be used/mated with electronic imaging system such as electronic imaging system 10.
  • Figures 5-7 more particularly illustrate elements of sample object stage 104 and an optical interface relative with the focal plane of camera/lens system 18.
  • Figure 5A shows a diagrammatic side view of sample object stage 104 showing the relative movement of a movable phosphor plate 125 according to the invention relative to the sample object stage.
  • Figure 5B shows a diagrammatic side view of the sample object stage in a first imaging position PI wherein phosphor plate 125 is disposed proximate the sample object stage and positioned for imaging light from a phosphor layer 132, shown in Fig. 6.
  • Figure 5C shows a diagrammatic side view of the sample object stage in the second imaging position P2 wherein phosphor plate 125 has been withdrawn to a position that is not proximate the sample object stage.
  • Figure 6 shows an enlarged, fragmentary sectional view taken along line 6-6 of Figure 5B , which corresponds with the first imaging position P 1.
  • Figure 7 shows an enlarged, fragmentary sectional view taken along line 7-7 of Figure 5C , which corresponds with the second imaging position P2.
  • sample object stage 104 includes a support member made up from an open frame 120 to support and stretch a thin plastic support sheet 122.
  • Support sheet 122 is selected so as to support the weight of a sample or object to be imaged and is made form a material that is optically clear and free of significant interfering fluorescence.
  • Phosphor plate 125 is mounted for motion toward and away from sample object stage 104. While those skilled in the art might recognize other configurations, in a preferred embodiment, phosphor plate 125 is mounted for translation to provide slidable motion (in the direction of arrow A in Figure 5A ) relative to frame 120, beneath the sample, in intimate contact with support sheet 122. Such motion can be accomplished using methods known to those skilled in the art, for example, frame 100 and phosphor plate 125 can be disposed on rails supported by a surface of an optical platen. As will be more particularly described below, in first imaging position P1, phosphor layer 130 in phosphor plate 125 is in overlapping arrangement with sample object stage 104 ( Figure 6 ) when an x-ray image of the object is captured.
  • phosphor plate 125 is translated/moved away from sample object stage 104 ( Figure 7 ) for capture of an image of the object such that phosphor plate 125 is not imaged when an image of the object is captured in second imaging position P2.
  • Figure 6 provides an enlarged view of sample object stage 104 including phosphor plate 125 to more particularly show a focal plane.
  • Sample support sheet 122 preferably comprises Mylar or polycarbonate and has a nominal thickness of about 0.1mm.
  • a protective layer 128 (for example, reflective Mylar) of about 0.025mm is provided on phosphor layer 130 to protect the surfaces of layer 130 during movement of phosphor plate 125.
  • Protective layer 128 promotes/increases the image-forming light output, m a preferred embodiment, protective layer 128 is reflective so as to prevent object reflection back into the image-forming screen, reducing the confusing the ionizing radiation image.
  • Phosphor layer 130 functions to transduce ionizing radiation to visible light practically managed by lens and camera system 18 (such as a CCD camera).
  • Phosphor layer 130 can have a thickness ranging from about 0.01 mm to about 0.1 mm, depending upon the application (i.e., soft x-ray, gamma-ray or fast electron imaging).
  • an optical layer 132 is provided for conditioning emitted light from phosphor layer 130.
  • Optical layer 132 can have a thickness in the range of less than about 0.001mm.
  • a supporting glass plate 134 is provided. Glass plate 134 is spaced at a suitable mechanical clearance from an optical platen 126, for example, by an air gap/void 136.
  • the surfaces of clear optical media e.g., a lower surface of glass plate 134 and both surfaces of optical platen 126) are provided with anti-reflective coating to minimize reflections that may confuse the image of the object.
  • Figure 7 provides an expanded view of sample object stage 13 including wherein phosphor plate 125 is removed (i.e., taken along line 7-7 of Figure 5C ). As shown in Figure 7 is frame 120, sample support sheet 122, an air gap/void 138 (since phosphor plate 125 is removed), and optical platen 126.
  • an object such as a small animal
  • An operator configures system 100 for imaging in a first mode, and an image of the object is captured using lens/camera system 18 in the first mode (step 202).
  • System 18 converts the light image into an electronic image which can be digitized.
  • This digitized image is referred to as Image 1 or I1.
  • the digitized image can be displayed on the display device, stored in memory, transmitted to a remote location, processed to enhance the image, and/or used to print a permanent copy of the image.
  • the object remains immobilized on sample object stage 104; no change in the position/location of the object is made.
  • the operator configures system 100 for imaging in a second mode (step 204), and an image of the object is captured using lens/camera system 18 in the second mode.
  • the resulting digitized image is referred to as Image2 or I2. Since the position of the object was not moved/changed during the capture of the images, both Image1 and Image2 can readily be merged or superimposed, using methods known to those skilled in the art, such that the two images are co-registered. As such, a third image can be generated comprising Image1 and Image2.
  • system 100 can be configured in several modes, including: x-ray imaging, bright-field imaging, dark-field imaging (including luminescence imaging, fluorescence imaging) and radioactive isotope imaging.
  • phosphor plate 125 is moved to position P1 in optical registration with sample object stage 104 (as shown in Figures 5B and 6 ).
  • x-ray source 102 is employed when capturing the image of the immobilized object.
  • phosphor plate 125 is moved to position P2, out of optical registration with sample object stage 104 (as shown in Figures 5C and 7 ), and an image of the immobilized object is appropriately captured.
  • the object is immobilized on sample object stage 104, and light emitted from the object (usually diffusive within the turbid constituents of a solid object) is projected to the object surface, which intimately bears upon the upper surface of sample support sheet 122.
  • the object surface is defined by a refractive boundary (e.g., the skin of an animal) that delineates the interior of the object (usually a heterogeneous, turbid media of higher index of refraction) and air.
  • a refractive boundary e.g., the skin of an animal
  • Light emanating from within an object e.g., luminescent or transmitted
  • projects to the surface from which it scatters defining the light that may be productively managed to create an image of the object.
  • light may be provided from beneath optical platen 126 and scattered from the object surface, thereby providing reflective light for imaging the same object.
  • the definition of the object boundary may be moderated by matching the refractive index of the object boundary to support sheet 122 by introducing an index-matching fluid (e.g., water).
  • an index-matching fluid e.g., water
  • the depth to which good focus can be achieved in optical imaging is dependent on minimizing the surface scatter of the object, and methods such as index matching and increasing wavelength (e.g., near-infrared, NIR imaging) are is well known in the art.
  • the depth to which good focus can be achieved in optical imaging is dependent on minimizing the surface scatter of the object, and methods such as index matching and increasing wavelength (e.g., near-infrared, NIR imaging) are well known in the art.
  • the emitted sample light can arise from luminescence, fluorescence or reflection, and the focal plane of the lens can be adjusted to the elevation of object surface.
  • the "light" can be ionizing radiation passing through or emitted from the object, or passing into the phosphor and forming an image.
  • Soft x-rays consistent with thin objects or small animals, project an image through the diffusive phosphor onto the optical boundary, adding the depth of the phosphor (more than about 0.02mm) to the depth of focus. More significant is the focal distance contributed by the phosphor support plate 134 , which maybe fractional millimeters, depending upon the thickness and index of the glass or plastic.
  • the fractional-millimeter elevation of the best focal plane contributed by the phosphor support can provide a better coincidence between the phosphor focal plane and the focal plane used for optical imaging.
  • the preferred/best focal plane may be located at millimeter depths into a nominally turbid object.
  • the phosphor support plate 134 can be thicker to maximize the coincidence of the optical and phosphor imaging planes.
  • Emitted gamma rays from a thick object are distributed over the plane of the phosphor, diffusing the image by millimeters, and an appropriately thick phosphor layer (about 0.1mm) may be preferred for increased detection efficiency. Consequently, the location of the focal plane at the supporting sheet is not critical to the resolution of the radio isotopic image. Better resolution and more precise planar projection of the emitting isotope can be achieved by gamma-ray collimation. Collimators of millimeter-resolution are available and capable of projecting isotopic location to millimeter resolution at the focal plane of the phosphor in the present invention.
  • the thickness of the layers in the focal plane of the lens is desirable.
  • fast lenses which are essential elements for the practice of imaging low-light emissions
  • less than about 0.2mm of spatial resolution is desirable, and a megapixel CCD camera (cooled) imaging at 100mm field is suitable.
  • more resolution is desirable.
  • Precision registration of the multi-modal image can be accomplished using methods known to those skilled in the art.
  • co-registered optical imaging is enabled by the same lens/camera system using epi-illumination methodologies at a sufficiently similar focal plane.
  • Figures 9A-9C show images captured using the apparatus and method of the present invention.
  • a mouse was immobilized on sample object stage 104 (step 200 of Figure 8 ) of system 100.
  • System 100 was first configured for NIR fluorescence imaging wherein phosphor plate 125 is removed from co-registration with frame 100.
  • a first image was captured and is displayed in Figure 9A (step 202 of Figure 8 ).
  • system 100 was configured for x-ray imaging wherein phosphor plate 125 is placed in co-registration with frame 100.
  • a second image was captured and is displayed in Figure 9B (step 204 of Figure 8 ).
  • the first and second images were merged (step 206 of Figure 8 ) and the merged image is displayed in Figure 9C .
  • the fluorescent signals superimposed on the anatomical reference clarify the assignment of signal to the bladder and an expected tumor in the neck area of this illustrated experimental mouse.
  • first and/or second image can be enhanced using known image processing methods/means prior to be merged together.
  • the merged image can be enhanced using known image processing methods/means. Often, false color is used to distinguish fluorescent signal from gray-scale x-rays in a merged image.
  • Figures 10A-10C provide a further example using the apparatus and method of the present invention.
  • Figure 10A is a NIR fluorescence image of a mouse while
  • Figure 10B is an x-ray image of the same immobilized mouse.
  • the first and second images were merged and the merged image is displayed in Figure 10C .
  • the first and second images were contrasted. This processing allows particular areas of the mouse to be visually enhanced for diagnostic purposes. For example, areas 150, 152, and 156 are potential secondary early detection sites, and area 154 shows the primary tumor injection site at the knee.
  • Figures 11A-11C provide yet a further example using the apparatus and method of the present invention.
  • Figure 11A is a near IR fluorescence image of a mouse wrist while
  • Figure 11B is an x-ray image of the same immobilized mouse wrist.
  • the first and second images were merged and the merged image is displayed in Figure 11C .
  • the merged image provides a diagnostic image for viewing a potential secondary tumor site. Note that this image set clearly demonstrates the precision to which the current invention enables the co-location of objects from differing imaging modes.
  • the maximum fluorescent signal emanating from a pre-metastatic tumor on the radius (arm-bone) tip at the wrist is within about 0.1 mm of the suspect lesion subsequently identified by microscopic histology.
  • a phosphor plate suitable for use with the apparatus and method of the present invention is disclosed in US Patent No. 6,444,988 (Vizard ) , commonly assigned and incorporated herein by reference.
  • a phosphor plate as described in Vizard is shown in Fig. 12 .
  • a suitable phosphor plate 125A for use with the apparatus and method of the present invention includes a transparent support 210 (such as glass) upon which is coated an interference filter 220 which is a multicoated short-pass filter designed to transmit light at a specified wavelength (and below) and reflect light above that wavelength.
  • Plate 125A also includes a thin phosphor layer 240 and a removable thick phosphor layer 260.
  • Thin phosphor layer 240 is used for high resolution imaging applications of ionizing radiation or for very low energy (self- attenuating) ionizing radiation such as low-energy electrons or beta particles.
  • Thick phosphor layer 260 is used for high energy ionizing radiation that freely penetrates the phosphor. Thick phosphor layer 260 is removable and is shown in Figure 12 overlaying thin phosphor layer 240. Layer 260 is removable to the position shown in dashed lines out of contact with layer 240.
  • the phosphor preferably used in phosphor layers 240 and 260 is Gadolinium Oxysulfide: Terbium whose strong monochromatic line output (544- 548 nanometers (NM) is ideal for co-application with interference optics.
  • This phosphor has technical superiority regarding linear dynamic range of output, sufficiently "live” or prompt emission and time reciprocity, and intrascenic dynamic range which exceed other phosphors and capture media.
  • This phosphor layer preferably has a nominal thickness of 10-30 micrometers ( ⁇ m) at 5-20 grams/square foot (g/ft2) of phosphor coverage, optimally absorbing 10-30 Kev x-rays.
  • Thick phosphor layer 260 has a nominal thickness of 100 ⁇ m at 80 g/ft2 of phosphor coverage.
  • duplex phosphor layers impart flexibility of usage for which the thick phosphor layer 260 may be removed to enhance the spatial resolution of the image.
  • Thin phosphor layer 240 intimately contacts filter 220, whereas thick phosphor layer 260 may be alternatively placed on thin phosphor layer 240.
  • Interference filter 220 transmits light at 551 NM and below and reflects light above that wavelength.
  • Filter 220 comprises layers of Zinc Sulfide-Cryolite that exhibits a large reduction in cutoff wavelength with increasing angle of incidence.
  • the filter has a high transmission at 540-551 NM to assure good transmission of 540-548 NM transmission of the GOS phosphor.
  • the filter also has a sharp short-pass cut-off at about 553 NM, that blue shifts at about 0.6 NM per angular degree of incidence to optimize optical gain.
  • Glass support 210 should be reasonably flat, clear, and free of severe defects.
  • the thickness of support 210 can be 2 millimeters.
  • the opposite side 280 of glass support 210 is coated with an anti-reflective layer (such as Magnesium Fluoride, green optimized) to increase transmittance and reduce optical artifacts to ensure that the large dynamic range of the phosphor emittance is captured.
  • an anti-reflective layer such as Magnesium Fluoride, green optimized
  • FIG. 13 shows steps of a method of producing phosphor layer 240.
  • a mixture of GOS:Tb in a binder is coated on a polytetrafluoroethylene (PTFE) support.
  • the PTFE support enables release of the coated phosphor layer from the PTFE support and subsequent use of the phosphor layer without support, since conventional supporting materials are an optical burden to phosphor performance.
  • an ultra thin (about 0.5 g/ft2 , 0.5 ⁇ m thick) layer of cellulose acetate overcoat can be applied to offer improved handling characteristics of the thin phosphor layer and to provide greater environmental protection to the underlying optical filter.
  • the phosphor layer is removed from the PFTE support.
  • the thin phosphor layer overcoated side is overlayed on interference filter 220. Clean assembly of the thin phosphor layer 240 and filter 220 assures an optical boundary that optimizes management of phosphor light output into the camera of the lens/camera system. Optical coupling of layer 240 and filter 220 is not necessary, since performance reduction may result.
  • layer 240 can be sealed around its periphery and around the periphery of filter 220 for mechanical stability and further protection of the critical optical boundary against environmental (e.g., moisture) intrusion.
  • environmental e.g., moisture
  • Advantages of the present invention include: provides anatomical localization of molecular imaging agent signals in small animals, organs, and tissues; provides precise co-registration of anatomical x-ray images with optical molecular and radio isotopic images using one system; promotes improved understanding of imaging agent's biodistribution through combined use of time lapse molecular imaging with x-ray imaging; and allows simple switching between multi-wavelength fluorescence, luminescence, radio-isotopic, and x-ray imaging modalities without moving the object/sample.

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Claims (5)

  1. Ein Abbildungssystem (100) zum Abbilden eines Objektes, wobei das Abbildungssystem ein Tragglied (104) umfasst, das in der Lage ist, das Objekt in einem immobilisierten Zustand aufzunehmen;
    eine Abbildungseinheit (12, 102, 106, 120, 122, 126) zum Abbilden des immobilisierten Objekts in einem ersten Abbildungsmodus zum Aufnehmen eines ersten Bildes (I1), wobei der erste Abbildungsmodus ausgewählt ist aus der Gruppe bestehend aus einem Röntgenstrahlmodus und einem Radioisotop-Modus und zum Abbilden des immobilisierten Objektes in einem zweiten Abbildungsmodus, der Licht von dem immobilisierten Objekt verwendet, und der sich von dem ersten Abbildungsmodus unterscheidet zum Aufnehmen eines zweiten Bildes (I2), wobei der zweite Abbildungsmodus ausgewählt ist aus der Gruppe bestehend aus Hellfeld-Modus, Fluoreszenz-Modus, und Lumineszenz-Modus; und ein Aufnahmesystem (18, 20, 22) zum Aufnehmen entweder des ersten Bildes oder des zweiten Bildes des Objekts, wobei das Abbildungssystem gekennzeichnet ist durch:
    eine bewegbare Phosphorplatte (125) zum Umwandeln ionisierender Strahlung in sichtbares Licht, wobei die Phosphorplatte angebracht ist, um bewegt zu werden, ohne das immobilisierte Objekt und das Tragglied zu bewegen, und zwar zwischen
    einer erste Position (P1) benachbart zum Tragglied für und während des Aufnehmens des ersten Bildes, und
    einer zweiten Position (P2), die nicht benachbart zum Drahtglied ist, und zwar während der Aufnahme des zweiten Bildes.
  2. Abbildungssystem nach Anspruch 1, das ferner eine Bildzusammenführungseinheit aufweist zum Erzeugen eines dritten Bildes durch Zusammenführung der ersten und zweiten Bilder (I1, I2).
  3. Abbildungssystem nach Anspruch 1, das ferner mehrere optische Elemente aufweist, welche die Anordnung einer gemeinsamen Brennebene, welche durch die ersten und zweiten Abbildungsmodi geteilt wird, zu ermöglichen.
  4. Verfahren zum Abbilden eines Objektes, das die folgenden Schritte aufweist:
    Vorsehen eines Traggliedes, das in der Lage ist das Objekt in einem immobilisierten Zustand aufzunehmen;
    Vorsehen einer Phosphorplatte, die bezüglich des Traggliedes bewegbar ist, und zwar ohne das immobilisierte Objekt und das Tragglied zu bewegen, und zwar zwischen einer ersten Position, in der die Phosphorplatte in optischer Ausrichtung mit dem Tragglied ist und einer zweiten Position, in der die Phosphorplatte nicht in optischer Ausrichtung mit dem Tragglied ist;
    Anordnung der Phosphorplatte in der ersten Position;
    Aufnehmen eines ersten Röntgenbildes oder eines ersten Radioisotopbildes des immobilisierten Objektes, wenn die Phosphorplatte in der ersten Position angeordnet ist;
    Bewegen der Phosphorplatte zu der zweiten Position; und
    Verwenden von Licht von dem Objekt zum Einfangen eines zweiten Dunkelfeld-Bildes oder eines zweiten Hellfeld-Bildes des immobilisierten Objektes, wenn die Phosphorplatte in der zweiten Position angeordnet ist.
  5. Verfahren nach Anspruch 4, das ferner die folgenden Schritte aufweist:
    Erzeugen eines dritten Bildes durch Zusammenführen der ersten und zweiten Bilder; und
    Anzeigen, Übertragen, Verarbeiten oder Drucken des dritten Bildes.
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